JPH0581253B2 - - Google Patents
Info
- Publication number
- JPH0581253B2 JPH0581253B2 JP28694190A JP28694190A JPH0581253B2 JP H0581253 B2 JPH0581253 B2 JP H0581253B2 JP 28694190 A JP28694190 A JP 28694190A JP 28694190 A JP28694190 A JP 28694190A JP H0581253 B2 JPH0581253 B2 JP H0581253B2
- Authority
- JP
- Japan
- Prior art keywords
- light
- blood
- glucose concentration
- blood glucose
- measuring device
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
- 239000008280 blood Substances 0.000 claims abstract description 75
- 210000004369 blood Anatomy 0.000 claims abstract description 75
- 238000005259 measurement Methods 0.000 claims abstract description 35
- WQZGKKKJIJFFOK-GASJEMHNSA-N Glucose Natural products OC[C@H]1OC(O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-GASJEMHNSA-N 0.000 claims abstract description 31
- 239000008103 glucose Substances 0.000 claims abstract description 31
- 230000005855 radiation Effects 0.000 claims abstract description 13
- 238000011088 calibration curve Methods 0.000 claims abstract description 4
- 230000003287 optical effect Effects 0.000 claims description 19
- 238000012360 testing method Methods 0.000 claims description 14
- 238000001514 detection method Methods 0.000 claims description 12
- 238000012545 processing Methods 0.000 claims description 6
- 230000008859 change Effects 0.000 claims description 5
- 238000004364 calculation method Methods 0.000 claims description 3
- 239000013307 optical fiber Substances 0.000 claims description 3
- 229910052732 germanium Inorganic materials 0.000 claims description 2
- GNPVGFCGXDBREM-UHFFFAOYSA-N germanium atom Chemical compound [Ge] GNPVGFCGXDBREM-UHFFFAOYSA-N 0.000 claims description 2
- 230000005494 condensation Effects 0.000 claims 1
- 238000009833 condensation Methods 0.000 claims 1
- 210000004204 blood vessel Anatomy 0.000 abstract description 15
- 238000000034 method Methods 0.000 abstract description 11
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 abstract description 6
- 239000004065 semiconductor Substances 0.000 abstract description 5
- 238000001307 laser spectroscopy Methods 0.000 abstract description 4
- 230000005540 biological transmission Effects 0.000 abstract description 3
- 230000005670 electromagnetic radiation Effects 0.000 abstract 4
- 230000003595 spectral effect Effects 0.000 abstract 2
- VRDIULHPQTYCLN-UHFFFAOYSA-N Prothionamide Chemical compound CCCC1=CC(C(N)=S)=CC=N1 VRDIULHPQTYCLN-UHFFFAOYSA-N 0.000 abstract 1
- 238000004458 analytical method Methods 0.000 description 6
- 238000010586 diagram Methods 0.000 description 4
- 230000000694 effects Effects 0.000 description 3
- 230000010355 oscillation Effects 0.000 description 3
- 210000000707 wrist Anatomy 0.000 description 3
- 238000004497 NIR spectroscopy Methods 0.000 description 2
- 239000012503 blood component Substances 0.000 description 2
- HVYWMOMLDIMFJA-DPAQBDIFSA-N cholesterol Chemical compound C1C=C2C[C@@H](O)CC[C@]2(C)[C@@H]2[C@@H]1[C@@H]1CC[C@H]([C@H](C)CCCC(C)C)[C@@]1(C)CC2 HVYWMOMLDIMFJA-DPAQBDIFSA-N 0.000 description 2
- 230000001678 irradiating effect Effects 0.000 description 2
- 238000012417 linear regression Methods 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 238000012067 mathematical method Methods 0.000 description 2
- 238000000926 separation method Methods 0.000 description 2
- 238000012795 verification Methods 0.000 description 2
- LFQSCWFLJHTTHZ-UHFFFAOYSA-N Ethanol Chemical compound CCO LFQSCWFLJHTTHZ-UHFFFAOYSA-N 0.000 description 1
- 230000003213 activating effect Effects 0.000 description 1
- 230000002411 adverse Effects 0.000 description 1
- 230000003321 amplification Effects 0.000 description 1
- 238000010241 blood sampling Methods 0.000 description 1
- 235000012000 cholesterol Nutrition 0.000 description 1
- 239000000306 component Substances 0.000 description 1
- 210000002808 connective tissue Anatomy 0.000 description 1
- 206010012601 diabetes mellitus Diseases 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 230000005284 excitation Effects 0.000 description 1
- 239000000835 fiber Substances 0.000 description 1
- 230000006870 function Effects 0.000 description 1
- 239000007924 injection Substances 0.000 description 1
- 238000002347 injection Methods 0.000 description 1
- 238000007689 inspection Methods 0.000 description 1
- 238000011835 investigation Methods 0.000 description 1
- 238000003199 nucleic acid amplification method Methods 0.000 description 1
- 230000008569 process Effects 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 238000004611 spectroscopical analysis Methods 0.000 description 1
- 230000009466 transformation Effects 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Physics & Mathematics (AREA)
- Medical Informatics (AREA)
- Surgery (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Veterinary Medicine (AREA)
- Molecular Biology (AREA)
- Optics & Photonics (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Emergency Medicine (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
- Investigating Or Analysing Biological Materials (AREA)
- Measuring Or Testing Involving Enzymes Or Micro-Organisms (AREA)
Abstract
Description
【発明の詳細な説明】
（産業上の利用分野）
この発明は血糖濃度測定装置に係り、特に従来
の測定装置のように注射器やメス等の器具を用い
て採血してから血糖濃度を測定するのではなく、
ノン・インベイシブ方法（Non−Invasive
Technique）を用いて採血等による生体の損傷を
伴わずに、単に本装置の測定部分（Port）を血
管の見える人体の適当な部分、例えば手首の内側
に当てることにより、血糖濃度の測定を可能にし
た生体を損なわない血糖濃度測定装置に関する。[Detailed Description of the Invention] (Industrial Application Field) This invention relates to a blood glucose concentration measuring device, and in particular, the present invention relates to a blood glucose concentration measuring device, and in particular, the blood glucose concentration is measured after blood is collected using an instrument such as a syringe or a scalpel, as in conventional measuring devices. rather than
Non-Invasive method
Blood sugar concentration can be measured by simply applying the measuring part (Port) of this device to an appropriate part of the human body where blood vessels are visible, such as the inside of the wrist, without causing damage to the living body due to blood collection etc. The present invention relates to a blood glucose concentration measuring device that does not harm living organisms.
通常、糖尿病等の患者は一日に２回ないし８回
程度、平均すると４回程度は注射器等により血液
を採取し、その後、例えば酵素法（Enzymatic
Method）を利用した携帯用血糖濃度測定機器に
より血液中の糖濃度を測定している。
Normally, patients with diabetes etc. collect blood with a syringe, etc., about 2 to 8 times a day, on average about 4 times.
The sugar concentration in the blood is measured using a portable blood glucose concentration measuring device using the method (Method).
現在、前記測定機器を用いて行なう検査及び測
定においては、１回の検査及び測定毎に使い捨て
の注射器や検査紙等が必らず１セツトは使用され
ている。従来の測定機器を用いる検査及び測定
は、機器の本体だけでも高価であるばかりでな
く、注射器や検査紙等の測定補助器具の購入費用
だけでも年間を通して計算すると多大な経費を要
している。 Currently, in tests and measurements performed using the above-mentioned measuring instruments, one set of disposable syringes, test strips, etc. are always used for each test or measurement. Inspection and measurement using conventional measuring equipment not only requires expensive equipment itself, but also the purchase cost of measurement aids such as syringes and test strips, which costs a large amount of money throughout the year.
このような問題を解消するため多くの研究が進
められてきた。 Many studies have been carried out to solve these problems.
本発明の目的は、血糖を測定する時に注射器・
試験紙等の器具を用いることなく血糖濃度測定用
の装置の測定部を単に皮膚に当てることにより、
手軽でかつ人体に悪影響を与えることなく血糖濃
度を測定することのできる、生体を損なわない血
糖濃度測定装置を提供することにある。
The purpose of the present invention is to use a syringe and a
By simply applying the measuring part of the device for measuring blood sugar concentration to the skin without using any instruments such as test strips,
It is an object of the present invention to provide a blood glucose concentration measuring device that is easy to use, can measure blood glucose concentration without adversely affecting the human body, and does not harm living organisms.
上記目的を達成するため、この発明による生体
を損なわない血糖濃度測定装置は、電源スイツチ
を介して所定電圧を供給する電源と、この電源に
より所定波長の光を発生させる光源と、この光源
からの光線を所定の平行光線に制御する光学系
と、光学系を介して供給された光線を被測定部位
に照射し反射されてきた光を集束させる集束部
と、集束部が集束した光を検出する検出部と、検
出部からの出力をアナログ信号からデイジタル信
号に変換した測定値を基準値と比較して演算処理
して血糖値を算出する演算処理部と、を備えた生
体を損なわない血糖濃度測定装置を、以下のよう
に構成したものである。
In order to achieve the above object, the blood glucose concentration measuring device according to the present invention that does not harm the living body includes a power source that supplies a predetermined voltage via a power switch, a light source that uses this power source to generate light of a predetermined wavelength, and a An optical system that controls the light beam into a predetermined parallel light beam, a focusing section that irradiates the measured part with the light beam supplied through the optical system and focuses the reflected light, and the focusing section detects the focused light. Blood sugar concentration that does not harm living organisms, comprising a detection unit and a calculation processing unit that calculates a blood sugar level by comparing the measured value obtained by converting the output from the detection unit from an analog signal to a digital signal with a reference value and calculating the blood sugar level. The measuring device was configured as follows.
少なくとも１つの発光素子よりなり接合部を備
えると共に前記電源から電流により異なる出力波
長の光を発生させる前記光源としてのレーザダイ
オードと；前記電源からの出力に基づいて電圧の
安定した出力を前記光源としてのレーザダイオー
ドに供給するダイオード用の電源調節器と；温度
変化の影響を受け易い前記レーザダイオードの接
合部に対して所定の割合で電流値を変化させるよ
うに制御する温度調節器と；前記電源調節器を制
御するために前記演算処理部より出力されるデイ
ジタル制御信号をアナログ制御信号に変換させる
Ｄ／Ａ変換器と；前記レーザダイオードから放出
された光を測定目的に応じて分離・結合させて平
行光線となるように光学的に調節する光学系と；
前記光学系により調節された光を被測定部位であ
る被測定者の皮膚に照射すると共に、血管内の血
液中の血糖分子の倍振動及び組み合わせ振動によ
り散乱されて反射した光を集束する集光部と；前
記集光部により集束された光子を電気的なアナロ
グ測定値信号に変換した後、この信号を増幅して
出力する検出器と；前記電気的なアナログ測定値
をデイジタル測定値に変換するＡ／Ｄ変換器と；
前記基準値としての検定曲線を記憶するメモリ
と；変換された前記デイジタル測定値と前記メモ
リに記憶された検定曲線とを比較して血液中の血
糖濃度を算出すると共に、前記Ｄ／Ａ変換器を介
して前記電源調節器及び温度調節器に制御信号を
出力してレーザダイオードの発光光線を制御する
前記演算処理部としてのマイクロコンピユータ
と；そして、前記マイクロコンピユータにより演
算・算出された血糖濃度を表示するデイジタルデ
イスプレイと；を具備すると共に、装置全体を携
帯可能な寸法及び形状に小型化して形成したもの
である。 a laser diode as the light source that is made up of at least one light emitting element and includes a junction and that generates light of different output wavelengths depending on the current from the power source; as the light source that outputs a stable voltage based on the output from the power source; a power supply regulator for a diode that supplies the laser diode; a temperature regulator that controls a junction part of the laser diode that is susceptible to temperature changes to change a current value at a predetermined rate; a D/A converter that converts a digital control signal output from the arithmetic processing unit into an analog control signal in order to control the regulator; and a D/A converter that separates and combines the light emitted from the laser diode according to the purpose of measurement. an optical system that optically adjusts the rays so that they become parallel rays;
The light adjusted by the optical system is irradiated onto the skin of the person being measured, which is the part to be measured, and the light that is scattered and reflected by the double vibration and combination vibration of blood sugar molecules in the blood within the blood vessel is focused. a detector that converts the photons focused by the light condensing section into an electrical analog measurement value signal, and then amplifies and outputs this signal; converts the electrical analog measurement value into a digital measurement value; an A/D converter;
a memory for storing a test curve as the reference value; a blood glucose concentration in the blood is calculated by comparing the converted digital measurement value with the test curve stored in the memory, and the D/A converter a microcomputer as the arithmetic processing unit that outputs a control signal to the power supply regulator and temperature regulator to control the light emitted by the laser diode; The device is equipped with a digital display for displaying images, and the entire device is miniaturized to a size and shape that is portable.
（作用）
この発明は、近赤外線拡散反射レーザー分光法
（Near−Infrared Radiation Diffuse−
Reflection Laser Spectroscopy）に基づいて、
人体に悪影響を与えない周波数を有する電子輻射
線を血管に照射し、血糖濃度を測定するようにし
たものであり、皮膚の表面から測定部位の血管ま
でを通過し得る波長を有する電子輻射線を用いて
いる。この皮膚から血管までは、“ウオーターウ
インドウ（Water Window）”と呼ばれている
が、これは人体の結合組織の大部分が水分
（H2O）より構成されているため名付けられたも
のである。この“ウオーターウインドウ”を通過
できる電子輻射線の波長は3μｍ〜5μｍの範囲内
に部分的に散在していることが知られている。と
ころで、最近本願発明者らが調査・研究した結果
によれば、人体に有害でない適切なエネルギーを
持つ電子輻射線を皮膚に照射したときに“ウオー
ターウインドウ”を通過して血管まで到達できる
波長は1.3μｍ〜1.9μｍの範囲にあるということが
判明した。(Function) This invention provides near-infrared diffuse reflection laser spectroscopy.
Reflection Laser Spectroscopy)
Blood glucose concentration is measured by irradiating blood vessels with electronic radiation that has a frequency that does not have a negative effect on the human body, and uses electronic radiation that has a wavelength that can pass from the surface of the skin to the blood vessels at the measurement site. I am using it. This area from the skin to the blood vessels is called the "Water Window", so named because most of the connective tissue in the human body is composed of water (H 2 O). . It is known that the wavelengths of electron radiation that can pass through this "water window" are partially scattered within the range of 3 .mu.m to 5 .mu.m. By the way, according to the results of recent investigations and research by the inventors of the present application, when the skin is irradiated with electronic radiation having appropriate energy that is not harmful to the human body, the wavelength that can pass through the "water window" and reach the blood vessels is It was found that it was in the range of 1.3 μm to 1.9 μm.
従つて、本発明では半導体（ダイオード）レー
ザを使用して1.3μｍ〜1.9μｍの範囲、とりわけ
1.4μｍ〜1.8μｍの範囲の波長を有する電子輻射線
を利用している。この電子輻射線を照射したとき
に皮膚を通過して血管に到達する電子輻射線は、
血液の成分と相互作用し、血液の成分を成す分子
の固有の特性等により吸収されて散乱・反射され
る。従つて、本発明においては複雑な分子等に基
づく血液の不均一性（heterogeneity）により吸
収されて散乱・反射される光を本発明の目的に合
致するように設計された集光部（integrating
sphere−積分球）により集束し、この集束された
光子（hν）を検出部により電気的なアナログ測
定値に変換させた後、ワンチツプのマイクロコン
ピユータに供給し、このマイクロコンピユータに
供給し、このマイクロコンピユーターにより適切
な検定方法を用いて血糖値を計算・算出して血糖
濃度を測定できるようにしている。 Therefore, in the present invention, a semiconductor (diode) laser is used to obtain a laser beam in the range of 1.3 μm to 1.9 μm, especially
Electron radiation having a wavelength in the range of 1.4 μm to 1.8 μm is utilized. When this electron radiation is irradiated, the electron radiation that passes through the skin and reaches the blood vessels is
It interacts with blood components and is absorbed, scattered, and reflected due to the unique characteristics of the molecules that make up the blood components. Therefore, in the present invention, light that is absorbed, scattered, and reflected due to the heterogeneity of blood due to complex molecules, etc. is collected using an integrating section designed to meet the purpose of the present invention.
sphere (integrating sphere), the focused photons (hν) are converted into electrical analog measured values by the detector, and then supplied to a one-chip microcomputer; The computer calculates and calculates the blood sugar level using an appropriate testing method, making it possible to measure the blood sugar concentration.
尚、本発明において、近赤外線（Near
Infrared Radiation）の一般な特性は国際純粋化
学・応用化学連合会（IUPAC；International
Union of Pure and Applied Chemistry）によ
り定義された内容に準じている。即ち、その周波
数（sec-1）は1013〜3.75×1014Hzであり、そのエ
ネルギーは0.951〜35.8（Kcal／mol）、0.412〜
1.55eVであり、波長は0.8〜30μｍである。さらに
本発明は分子の振動、回転、並進運動による近赤
外線分光法において、血糖分子の振動運動に対す
る物理化学的な原理に基づいて、倍振動
（Overtonevibration）と組合わせ振動
（Combination vibration）を用いており、特に
倍振動が主に利用されている。 In addition, in the present invention, near infrared rays (Near
The general characteristics of Infrared Radiation are the International Union of Pure and Applied Chemistry (IUPAC).
According to the content defined by the Union of Pure and Applied Chemistry). That is, its frequency (sec -1 ) is 10 13 to 3.75×10 14 Hz, and its energy is 0.951 to 35.8 (Kcal/mol), 0.412 to
It is 1.55 eV and the wavelength is 0.8 to 30 μm. Furthermore, the present invention uses overtone vibration and combination vibration in near-infrared spectroscopy based on vibrational, rotational, and translational motion of molecules, based on the physicochemical principle of vibrational motion of blood sugar molecules. In particular, double vibration is mainly used.
一方、本発明による他の分析方法においては、
分光法における重要な測定値の処理と測定しよう
とする寸法（血糖濃度）等の計算処理のため、多
重線形回帰分析（multiple linear regression
analysis）と多変量分布分析（multivariate
analysis）等のような数学的な方法に基づいて本
発明の目的に合致するように本発明者らにより改
良された方法を用いてデータ処理・算出してい
る。 On the other hand, in other analysis methods according to the present invention,
Multiple linear regression analysis is used to process important measured values in spectroscopy and calculate the dimensions to be measured (blood sugar concentration), etc.
analysis) and multivariate distribution analysis
The data is processed and calculated using a method improved by the inventors to meet the purpose of the present invention based on mathematical methods such as
本発明によれば、検査方法が簡便であり誰でも
手軽に使用することができ、経費が少なくて済む
等の長所を持つ血糖濃度測定装置を提供できるこ
とになる。例えば、患者が外出や旅行をする時、
常時携帯することを必要としていた使い捨ての注
射器や試験紙等を携帯しなくて済むことになる。
さらに、上述したような採血等の検査を行なう為
の場所を捜さなくても済むようになる。さらにま
た、長期間にわたり検査及び測定を継続して行な
う場合には注射により人体の特定部分、例えば下
摶部等に変形が生じてしまい人体を害するという
問題点があつたが、これも克服することができ
る。 According to the present invention, it is possible to provide a blood glucose concentration measuring device that has advantages such as a simple testing method, anyone who can use it easily, and low cost. For example, when a patient goes out or travels,
This eliminates the need to carry disposable syringes, test strips, etc., which were required to be carried at all times.
Furthermore, there is no need to search for a place to conduct tests such as blood sampling as described above. Furthermore, when testing and measurement are carried out continuously over a long period of time, injections can cause deformation of certain parts of the human body, such as the lower part of the body, causing harm to the human body, but this problem can also be overcome. be able to.
本発明による生体を損なわない（ノン・インベ
イシブ）血糖濃度測定装置は直径が例えば0.5〜
５mmの範囲内、望ましくは２mm以下の測定部を、
例えば手首の内側等の皮膚上の血管が見える所定
部位に当接することにより、短時間内（例えば60
秒以内、望ましくは40秒以内）に血糖濃度を測定
できるので、従来のように不便で、なおかつ多大
の費用を必要とする使い捨ての注射器・試験紙等
の消耗器具を不要にすることができる。 The non-invasive blood glucose concentration measuring device according to the present invention has a diameter of, for example, 0.5~
The measuring part within the range of 5 mm, preferably 2 mm or less,
For example, by contacting a predetermined area on the skin where blood vessels are visible, such as the inside of the wrist, it can be applied within a short period of time (for example, 60
Blood glucose concentration can be measured within seconds (preferably within 40 seconds), eliminating the need for conventional consumable instruments such as disposable syringes and test strips that are inconvenient and costly.
以下、図面を参照して本発明の一実施例を詳細
に説明する。
Hereinafter, one embodiment of the present invention will be described in detail with reference to the drawings.
第１図は本発明による血糖濃度の測定装置のブ
ロツク構成図を示し、第２図は第１図に示された
血糖濃度の測定装置を詳細に示した回路図であ
る。図において、電源スイツチ１がオンされる
と、電源としての図示されないバツテリからワン
チツプで構成されたマイクロコンピユータ（以
下、マイコンという。）２に電圧が供給される。
これと同時に、前記電源はデイジタルデイスプレ
イ３、レーザダイオード用の電源調節器４、及び
検出部７にも供給され、必要に応じて光学系６等
にも供給される。この電源としてのバツテリは一
般には4.5V〜9Vのものが使用され、最も好まし
いのは充電用の6Vのものである。 FIG. 1 shows a block diagram of a blood glucose concentration measuring device according to the present invention, and FIG. 2 is a circuit diagram showing the blood glucose concentration measuring device shown in FIG. 1 in detail. In the figure, when a power switch 1 is turned on, voltage is supplied from a battery (not shown) as a power source to a microcomputer (hereinafter referred to as microcomputer) 2, which is constructed of a single chip.
At the same time, the power is supplied to the digital display 3, the power supply regulator 4 for the laser diode, and the detection unit 7, and also to the optical system 6 and the like as required. Generally, a battery of 4.5V to 9V is used as a power source, and a 6V battery for charging is most preferable.
この状態でスタート／リセツトスイツチ８がオ
ンされると、前記マイコン２は前記電源調節器４
に制御信号を供給し、これにより電源調節器４は
レーザダイオード５に電源を供給し始める。この
電源の供給開始により次第に増加した電流が臨界
電流（threshold current；約20ｍＡ）を越える
とレーザダイオード５が発光する。このときの電
流値は、現在の技術水準においてはレーザダイオ
ードの特性により安定した電圧と所定の温度のも
とで約20〜200ｍＡが適当な値であり、この電流
範囲の間で徐々に電流を上げて、予め定められた
電流値に達したときに測定に必要な波長を有する
光が放出されることになる。例えば、1.3μｍ〜
1.9μｍの範囲内の波長を有する光が用いられる
が、この中でも特に、1.4μｍ〜1.8μｍの波長を有
する光が主として有用である。光源として用いら
れる前記レーザーダイオード５は１個でも良い
が、通常複数個例えば30個程度で構成され、その
全てが同一波長の光を放出するようにしても良い
し、また、夫々が異なる波長の光を放出するよう
にしても良い。 When the start/reset switch 8 is turned on in this state, the microcomputer 2
The power regulator 4 starts supplying power to the laser diode 5 by supplying a control signal to the laser diode 5 . When the current that gradually increases with the start of the power supply exceeds a threshold current (approximately 20 mA), the laser diode 5 emits light. The appropriate current value at this time is approximately 20 to 200 mA at a stable voltage and given temperature due to the characteristics of the laser diode at the current level of technology, and the current is gradually increased within this current range. When the current value reaches a predetermined value, light having a wavelength necessary for measurement is emitted. For example, 1.3 μm ~
Light having a wavelength within the range of 1.9 .mu.m is used, of which light having a wavelength of 1.4 .mu.m to 1.8 .mu.m is primarily useful. The number of laser diodes 5 used as a light source may be one, but it is usually composed of a plurality of laser diodes, for example, about 30, all of which may emit light of the same wavelength, or each of which may emit light of a different wavelength. It may also be configured to emit light.
前記レーザダイオード５はいわゆる半導体レー
ザを生成するものであり、この半導体レーザの発
振波長域は、およそ0.33μｍ〜32μｍにわたつてい
る。ダイイオードレーザの場合、0.57μｍより短
波長側では実用性に適するものが開発されていな
い。半導体レーザにおいて発振波長の同調を行な
うには一般に、(a)材料の禁制帯幅の変化と、(b)材
料の屈折率の変化を利用する２つの方法があり、
前者は帯域同調に、後者は微細同調に主として用
いられている。後者の微細同調を行なう方法は屈
折率が圧力・磁界・温度等に依存しているため、
これらを制御することにより共振器の長さを等価
的に変化させて共振モードの周波数を変移させ
る。ダイオードレーザの場合、励起電流により
pn接合部に温度変化が生じ電流増加に伴い所定
の割合で発振周波数が低い方にシフトすることが
ある。温度調節器１３は、レーザダイオード５の
接合部分の温度変化に起因する上述のような影響
を除去するために、接合部の温度の調節を行なう
ものである。この温度調節は、レーザダイオード
５のチツプの外部から電流変化に伴う温度変化を
検出し、所望のチツプ温度になるように熱源を作
用させることにより行なわれる。 The laser diode 5 generates a so-called semiconductor laser, and the oscillation wavelength range of this semiconductor laser extends from approximately 0.33 μm to 32 μm. In the case of diode lasers, no one suitable for practical use has been developed at wavelengths shorter than 0.57 μm. There are generally two methods for tuning the oscillation wavelength in a semiconductor laser: (a) changes in the forbidden band width of the material, and (b) changes in the refractive index of the material.
The former is mainly used for band tuning, and the latter for fine tuning. The latter method of fine tuning is based on the fact that the refractive index depends on pressure, magnetic field, temperature, etc.
By controlling these, the length of the resonator is equivalently changed and the frequency of the resonance mode is shifted. For diode lasers, the excitation current
As a temperature change occurs in the pn junction and the current increases, the oscillation frequency may shift to a lower level at a predetermined rate. The temperature regulator 13 adjusts the temperature of the junction of the laser diode 5 in order to eliminate the above-mentioned effects caused by temperature changes at the junction. This temperature adjustment is performed by detecting a temperature change accompanying a current change from outside the chip of the laser diode 5, and activating a heat source to bring the chip temperature to a desired temperature.
複数個の前記レーザダイオード５から放出され
た光は同時または順次に発光するが、同時発光の
場合、例えばフーリエ変換を用いて必要な波長を
分離する。 The light emitted from the plurality of laser diodes 5 is emitted simultaneously or sequentially, but in the case of simultaneous emission, necessary wavelengths are separated using, for example, Fourier transformation.
前記レーザダイオード５よりなる光源から放出
された光は光学系６に達し、測定目的に合致する
平行光となるように分離・結合等の光学的調整が
行われる。この光学的な調整により一つ又は複数
の方向に光軸に調整された光線は、例えば積分球
より成る集光部９に供給され、これを通過して被
測定者の皮膚に順次に照射される。集光部９は積
分球とも呼ばれるようにほぼ球形の形状を有して
いる。 The light emitted from the light source consisting of the laser diode 5 reaches an optical system 6, where optical adjustments such as separation and combination are performed so that it becomes parallel light that meets the purpose of measurement. The light rays whose optical axis has been adjusted in one or more directions by this optical adjustment are supplied to a condensing unit 9 made of, for example, an integrating sphere, pass through this, and are sequentially irradiated onto the skin of the person to be measured. Ru. The light condensing section 9 has a substantially spherical shape, also called an integrating sphere.
ここで、光線の照射箇所を明確にするために被
測定者の皮膚上に照射範囲を示す基準ポートを予
め準備しておいても良いが、照射箇所がはつきり
している場合には基準ポートを設けることなく直
接皮膚に照射しても良い。この光線は被測定者の
皮膚を透過して血管内の血液にまで至り、血液に
吸収されずに散乱・反射された光は再び集光部９
により集束されから、検出部７により検出され
る。なお、散乱・反射された光を集束する集光部
９の大きさは直径が2.56cm以下に形成されてお
り、望ましくは1.28cm以下、更に最も望ましいの
は0.64cm以下となるように形成されたものであ
る。前記したように検出された測定値はアナログ
値を有する電気的な計数値であり、これは検出部
７に接続された一般的な前段増幅器により増幅さ
れた後、Ａ／Ｄ変換器１１に転送され、デイジタ
ル測定値に変換される。 Here, in order to clarify the irradiation area of the light beam, a reference port indicating the irradiation range may be prepared on the subject's skin in advance, but if the irradiation area is clearly visible, the reference port may be prepared in advance. The skin may be irradiated directly without providing a port. This light beam passes through the subject's skin and reaches the blood in the blood vessels, and the light that is not absorbed by the blood and is scattered and reflected is returned to the condensing section 9.
The light is focused by the detector 7 and then detected by the detector 7. The size of the condensing part 9 that converges the scattered and reflected light is formed to have a diameter of 2.56 cm or less, preferably 1.28 cm or less, and most preferably 0.64 cm or less. It is something that The measured value detected as described above is an electrical count value having an analog value, which is amplified by a general pre-amplifier connected to the detection unit 7 and then transferred to the A/D converter 11. and converted to digital measurements.
前記Ａ／Ｄ変換器１１によりデイジタル値に変
換された測定信号は、前記マイコン２に供給さ
れ、このマイコン２により内蔵メモリに予め記憶
されている基準（検定曲線）値と比較されて血糖
濃度が計算・算出され、この結果がデイジタルデ
イスプレイ３に表示される。 The measurement signal converted into a digital value by the A/D converter 11 is supplied to the microcomputer 2, and the microcomputer 2 compares it with a reference (verification curve) value stored in advance in the built-in memory to determine the blood glucose concentration. The calculation is performed and the result is displayed on the digital display 3.
上記血糖濃度測定機器は、全体の大きさ（横・
縦・高さ）が170×80×25mm以下となるように形
成されており、さらに150×75×22mm以下が適当
であり、また130×70×20mm以下に形成されるの
が最も好ましい。 The above blood sugar concentration measuring device has a large size (horizontal and
The length/height) is formed to be 170 x 80 x 25 mm or less, more preferably 150 x 75 x 22 mm or less, and most preferably 130 x 70 x 20 mm or less.
一方、前記検出部７としてはポートダイオード
により構成することが望ましいが、現在の技術水
準では特に前段増幅器が接続されたゲルマニウム
検出器（Ce detector）により実施するのが最も
望ましい。 On the other hand, the detection section 7 is preferably configured with a port diode, but according to the current state of the art, it is most desirable to implement it with a germanium detector (Ce detector) to which a pre-stage amplifier is connected.
また前記光学系６は、例えば直径0.5〜５mm以
下（最も好ましいのは直径２mm以下）の構成部品
により形成され、光を集光・拡散させて平行光線
を形成する。平行光線の形成は、周知のコリメー
タレンズ等を用いて行なつてもよい。 The optical system 6 is formed of components having a diameter of, for example, 0.5 to 5 mm or less (most preferably a diameter of 2 mm or less), and condenses and diffuses light to form parallel rays. The parallel light beams may be formed using a well-known collimator lens or the like.
なお、本実施例では集光部９が球形に形成され
て場合についてのみ説明したが、本発明はこれに
限定されず、例えば断面が楕円形、半楕円形また
は他の図形となる三次元の立体形状に集光部９を
形成することもできる。 In this embodiment, only the case where the light condensing part 9 is formed in a spherical shape has been described, but the present invention is not limited to this. The condensing section 9 can also be formed in a three-dimensional shape.
さらに、本発明の血糖濃度測定装置は小型・軽
量のものであるためマイコン２及びレーザダイオ
ード５等の本体と集光部９及び検出部７等の測定
部分（port）とを一体的に形成しておいても十分
にその操作性を発揮できるが、本体と測定部分と
を２つの部分に分離して形成しても良い。分離さ
れている場合には、レーザダイオード５からの光
を被測定者の前記測定部分まで伝達するために、
光フアイバ等の光伝送手段を用いている。この光
伝送手段の繊維の距離は、100〜1000mmであり、
この中間の500mm程度が一般には適当であるが、
最も適当な距離は300mmである。 Furthermore, since the blood glucose concentration measuring device of the present invention is small and lightweight, the main body such as the microcomputer 2 and the laser diode 5, and the measurement portions (ports) such as the light condensing section 9 and the detecting section 7 are integrally formed. Although the main body and the measurement part can be separated into two parts, the main body and the measurement part can be formed separately. If separated, in order to transmit the light from the laser diode 5 to the measurement part of the subject,
Optical transmission means such as optical fibers are used. The fiber distance of this optical transmission means is 100 to 1000 mm,
A value in the middle of this range, about 500 mm, is generally appropriate, but
The most suitable distance is 300mm.
なお、本実施例においてはＤ／Ａ変換器１０及
びＡ／Ｄ変換器１１がワンチツプマイコン２と分
離された場合についてのみ説明したが、本発明は
これに限定されず、Ｄ／Ａ変換器１０及びＡ／Ｄ
変換器１１がマイコン２に含まれた専用チツプを
用いても良い。 In this embodiment, only the case where the D/A converter 10 and the A/D converter 11 are separated from the one-chip microcomputer 2 has been described, but the present invention is not limited to this, and the D/A converter 10 and the A/D converter 11 are 10 and A/D
The converter 11 may be a dedicated chip included in the microcomputer 2.
なお、上述部分では測定値を比較する基準値と
しての検定曲線を内蔵メモリに格納しておくもの
として説明したが、本実施例はマイコン２の動作
を補助するためRAM１２1とEPROM１２2から
なる補助回路１２を用いて必要な情報の記憶・読
出しを行なうようにしても良い。 In addition, in the above part, it was explained that the verification curve as a reference value with which measured values are compared is stored in the built-in memory, but in this embodiment, in order to assist the operation of the microcomputer 2, an auxiliary system consisting of RAM 12 1 and EPROM 12 2 is used. The circuit 12 may be used to store and read out necessary information.
また、本実施例では血糖濃度の測定についての
み説明したが、本発明はこれに限らず、例えばコ
レステロール濃度あるいはアルコール濃度の測定
にも適用することができる。 Further, although this embodiment has described only the measurement of blood sugar concentration, the present invention is not limited to this, and can also be applied to, for example, measurement of cholesterol concentration or alcohol concentration.
上記構成に係るこの発明の一実施例による動作
は以下の各段階を経て行われる、電源スイツチ１
を利用してバツテリから電源を要するマイクロコ
ン２とデジタルデイスプレイ３、レーザダイオー
ド用電源調節器４、検出部７及び必要によつて光
学系６等にそれぞれ電源を供給する段階。 The operation of the embodiment of the present invention having the above configuration is performed through the following steps.
The step of supplying power to the microcomputer 2, digital display 3, laser diode power regulator 4, detection unit 7, optical system 6, etc. as necessary, using the power supply from the battery.
スタート／リセツトスイツチ８を用いてマイコ
ン２によりレーザダイオード用電源調節器４及び
温度調節器１３がレーザダイオード５に安定した
電圧と温度で電流を漸増的に印加して測定に必要
な波長を放出するように制御する段階。 Using the start/reset switch 8, the microcomputer 2 causes the laser diode power regulator 4 and temperature regulator 13 to gradually apply current to the laser diode 5 at a stable voltage and temperature to emit the wavelength necessary for measurement. The stage to control.
これと関連してマイクロコンピユータ２とレー
ザダイオード用電源調節器４との間に設けられた
Ｄ／Ａ変換器１０によりデイジタル制御信号を電
気的な制御信号に変換させる段階。 In connection with this, the digital control signal is converted into an electrical control signal by the D/A converter 10 provided between the microcomputer 2 and the laser diode power supply regulator 4.
レーザダイオード５がレーザダイオード用電源
調節器４の制御により測定に必要な波長の光を放
射する段階。 A stage in which the laser diode 5 emits light of a wavelength necessary for measurement under the control of the laser diode power supply regulator 4.
前記レーザダイオード５から放射された光を光
学系６により目的に合うように平行にするかある
いは光学的に調節及び分離または結合させる段
階。 collimating or optically adjusting and separating or combining the light emitted from the laser diode 5 by means of an optical system 6;
この光学的に調節された光を集光部９を通じて
血糖濃度を測定しようとする被測定者の血管が見
える皮膚に照射する段階。 The step of irradiating this optically adjusted light through the condensing section 9 onto the skin of the person whose blood sugar concentration is to be measured, where blood vessels are visible.
皮膚を通過して血管まで到達され血液により吸
収、散乱、反射された光を集光部９を通じて集束
する段階。 A step in which the light that has passed through the skin, reached the blood vessels, and been absorbed, scattered, and reflected by the blood is focused through the condenser 9.
前記集光部９により集束された光子を検出部７
により検出して電気的なアナログ測定値に変換
し、検出部７に設けられた前段増幅部で増幅した
後、Ａ／Ｄ変換器１１に転送する段階。 The photons focused by the light condensing unit 9 are sent to the detection unit 7.
A step of detecting the measured value and converting it into an electrical analog measurement value, amplifying it in a pre-amplification section provided in the detection section 7, and then transmitting it to the A/D converter 11.
前記Ａ／Ｄ変換器１１を用いて前記電気的なア
ナログ測定値をデイジタル測定値に変換した後、
このデイジタル測定値をマイコン２に転送する段
階。 After converting the electrical analog measurement value into a digital measurement value using the A/D converter 11,
The stage of transmitting this digital measurement value to the microcomputer 2.
前記マイコン２内のメモリ領域に記憶されてい
る検定曲線と前記Ａ／Ｄ変換器１１により変換さ
れたデイジタル測定値を比較して血液中の血糖濃
度を計算、算出する段階。 A step of comparing the calibration curve stored in the memory area of the microcomputer 2 with the digital measurement value converted by the A/D converter 11 to calculate the blood glucose concentration in the blood.
この様に算出された血糖濃度をデイジタルデイ
スプレー３に表示する段階。 A step of displaying the blood sugar concentration calculated in this way on the digital display 3.
また、血糖濃度の測定方法は、近赤外線拡散反
射レーザー分光法に基づき、分子の振動、回転、
並進運動による近赤外線分光法で血糖分子の振動
運動に対する物理化学的原理に基づき、その中で
も倍振動と組合振動を利用し、特に倍振動を利用
するようになつたことをも特徴としている。 In addition, the method for measuring blood sugar concentration is based on near-infrared diffuse reflection laser spectroscopy.
Near-infrared spectroscopy using translational motion is based on the physicochemical principle of the vibrational motion of blood sugar molecules, and is characterized by the use of double vibrations and combined vibrations, especially double vibrations.
さらに、血糖濃度の測定方法は、前記マイコン
２内のメモリ領域に記憶されている検定曲線と前
記Ａ／Ｄ変換器１１により変換されたデジタル測
定値を比較して血糖濃度を計算、算出する段階で
多重線形回帰分析と多変量分布分析などの数学的
な方法を使用するようになつたことも特徴として
いる。 Furthermore, the method for measuring blood sugar concentration includes the step of calculating the blood sugar concentration by comparing the calibration curve stored in the memory area of the microcomputer 2 with the digital measurement value converted by the A/D converter 11. It is also characterized by the use of mathematical methods such as multiple linear regression analysis and multivariate distribution analysis.
前述したように、血糖濃度測定装置の本体と前
記測定部との間を光繊維を用いて分離する場合に
は、その分離される距離は100〜1000mmであり、
適当には500mm、最も適当には300mmである。 As mentioned above, when the main body of the blood sugar concentration measuring device and the measuring section are separated using an optical fiber, the separation distance is 100 to 1000 mm,
A suitable length is 500 mm, most suitably 300 mm.
以上詳細に説明したように、本発明によるノ
ン・インベイシブ血糖濃度の測定方法およびその
装置によれば、注射針のような器具を使用して血
液を採る必要もなく単に本装置の測定部分
（port）を血管の見える人体の適当な部分、例え
ば手首の内側に当てることにより血糖濃度を測定
できるようになつているため、簡便なおかつ身体
部位の変異などのような人体への有害さが無く、
従来の１回用注射器が要らなくなり、下級装備に
よる費用が殆どかからなくなる等の長所を有して
いる。
As explained in detail above, according to the method and device for measuring non-invasive blood glucose concentration according to the present invention, there is no need to collect blood using an instrument such as a syringe needle, and the measurement portion (port) of the device is simply used. ) can be applied to an appropriate part of the human body where blood vessels are visible, such as the inside of the wrist, to measure blood sugar concentration, which is simple and does not cause harm to the human body such as changes in body parts.
It has advantages such as eliminating the need for conventional single-use syringes and almost eliminating the cost of lower-grade equipment.
第１図は本発明による血糖濃度の測定装置のブ
ロツク構成図、第２図は第１図に示された血糖濃
度の測定装置を詳細に示した回路ブロツク図であ
る。
１……電源スイツチ、２……ワンチツプマイク
ロコンピユータ、３……デジタルデイスプレイ、
４……レーザダイオード用電源調節器、５……レ
ーザダイオード、６……光学系、７……検出部、
８……スタート／リセツトスイツチ、９……集光
部、１０……Ｄ／Ａ変換器、１１……Ａ／Ｄ変換
器、１２……補助回路、１２1……RAM、１２2
……EPROM、１３……温度調節器。
FIG. 1 is a block diagram of a blood glucose concentration measuring device according to the present invention, and FIG. 2 is a circuit block diagram showing the blood glucose concentration measuring device shown in FIG. 1 in detail. 1...Power switch, 2...One-chip microcomputer, 3...Digital display,
4... Laser diode power regulator, 5... Laser diode, 6... Optical system, 7... Detection unit,
8...Start/reset switch, 9...Light collector, 10...D/A converter, 11...A/D converter, 12...Auxiliary circuit, 12 1 ...RAM, 12 2
...EPROM, 13...Temperature controller.
Claims (1)
源と、この電源により所定波長の光を発生させる
光源と、この光源からの光線を所定の平行光線に
制御する光学系と、光学系を介して供給された光
線を被測定部位に照射し反射されてきた光を集束
させる集光部と、集光部が集束した光を検出する
検出部と、検出部からの出力をアナログ信号から
デイジタル信号に変換した測定値を基準値と比較
して演算処理して血糖値を算出する演算処理部
と、を備えた生体を損なわない血糖濃度測定装置
において、 少なくとも１つの発光素子より成り、かつ接合
部を備えると共に前記電源からの電流により異な
る出力波長の光を発生させる前記光源としてのレ
ーザダイオードと； 前記電源からの出力に基づいて電圧の安定した
出力を前記光源としてのレーザダイオードに供給
するダイオード用の電源調節器と； 温度変化の影響を受易い前記レーザダイオード
の接合部に対して所定の割合で電流値を変化させ
るようにこのダイオードが封止されたチツプの温
度を制御する温度調節器と； 前記電源調節器を制御するために前記演算処理
部より出力されるデイジタル制御信号をアナログ
制御信号に変換させるＤ／Ａ変換器と； 前記レーザーダイオードから放出された光を測
定目的に応じて分離・結合させて平行光線となる
ように光学的に調節する光学系と； 前記光学系により調節された光を被測定部位で
ある被測定者の皮膚に照射すると共に、血管内の
血液中の血糖分子の倍振動及び組み合わせ振動に
より散乱されて反射した光を集束する集光部と； 前記集光部により集束された光子を電気的なア
ナログ測定値信号に変換した後、この信号を増幅
して出力する検出器と； 前記電気的なアナログ測定値をデイジタル測定
値に変換するＡ／Ｄ変換器と； 前記基準値としての検定曲線を記憶するメモリ
と； 変換された前記デイジタル測定値と前記メモリ
に記憶された検定曲線とを比較して血液中の血糖
濃度を算出すると共に、前記Ｄ／Ａ変換器を介し
て前記電源調節器及び温度調節器に制御信号を出
力してレーザダイオードの発光光線を制御する前
記演算処理部としてのマイクロコンピユータと；
そして、 前記マイクロコンピユータにより演算・算出さ
れた血糖濃度を表示するデイジタルデイスプレイ
と； を具備すると共に、 装置全体を携帯可能な寸法及び形状に小型化し
て形成したことを特徴とする生体を損なわない血
糖濃度の測定装置。 ２ 前記レーザーダイオードから放射される電子
輻射線の波長が、1.4μｍ〜1.8μｍであり、この波
長の光が被測定者の皮膚を介して順次に血液に照
射されることを特徴とする特許請求の範囲第１項
に記載の生体を損なわない血糖濃度測定装置。 ３ 前記集光部は、直径が2.56mm以下のほぼ球形
に形成された積分球より成り、かつ、全体の寸法
が横150mm、縦75mm、及び高さ22mm以下に形成さ
れたことを特徴とする特許請求の範囲第１項項記
載の生体を損なわない血糖濃度測定装置。 ４ この血糖濃度測定装置の本体と、前記光学
系、集光部及び検出部より成る測定部とを分離し
て構成すると共に、前記本体及び前記測定部殿間
を光フアイバにより接続したことを特徴とする特
許請求の範囲第１項記載の生体を損なわない血糖
濃度測定装置。 ５ 前記集光部により集束された前記光子を検出
する検出部は、ポートダイオードを用いると共に
前段増幅器を備えたたゲルマニウム検出器より構
成され、前記Ｄ／Ａ変換器及びＡ／Ｄ変換器は、
前記マイクコンピユータから分離されて同一基板
上に実装され、かつ、前記電源としては4.5V〜
9Vの充電用バツテリより構成されていること特
徴とする特許請求の範囲第１項に記載の生体を損
なわない血糖濃度の測定装置。[Scope of Claims] 1. A power source that supplies a predetermined voltage via a power switch, a light source that uses this power source to generate light of a predetermined wavelength, and an optical system that controls the light beam from this light source into a predetermined parallel light beam. A condensing section that irradiates the light beam supplied through the optical system onto the measurement site and focuses the reflected light, a detection section that detects the light focused by the condensation section, and an analog output from the detection section. A blood sugar concentration measuring device that does not harm living organisms and is equipped with a calculation processing unit that calculates a blood sugar level by comparing a measured value converted from a signal to a digital signal with a reference value and calculating the blood sugar level, comprising at least one light emitting element. and a laser diode as the light source which includes a junction and generates light of different output wavelengths depending on the current from the power source; and a laser diode as the light source which outputs a stable voltage based on the output from the power source. a power supply regulator for the diode to be supplied; controlling the temperature of the chip in which the diode is sealed so as to change the current value at a predetermined rate for the junction of the laser diode that is susceptible to temperature changes; a temperature controller; a D/A converter that converts a digital control signal output from the arithmetic processing unit into an analog control signal in order to control the power supply controller; and a D/A converter that converts the light emitted from the laser diode into an analog control signal. an optical system that optically adjusts the light rays by separating and combining them to form parallel light beams according to the conditions; a light concentrator that focuses light scattered and reflected by double and combined vibrations of blood sugar molecules in the blood; and after converting the photons focused by the light concentrator into an electrical analog measured value signal, this signal is an A/D converter that converts the electrical analog measurement value into a digital measurement value; a memory that stores the calibration curve as the reference value; and the converted digital measurement value. The blood sugar concentration in the blood is calculated by comparing the value with the test curve stored in the memory, and a control signal is output to the power supply regulator and temperature regulator via the D/A converter to generate a laser beam. a microcomputer as the arithmetic processing unit that controls the light emitted from the diode;
and a digital display that displays the blood glucose concentration calculated and computed by the microcomputer; and a blood glucose device that does not damage living organisms, characterized in that the entire device is miniaturized to a portable size and shape. Concentration measuring device. 2. A patent claim characterized in that the wavelength of the electron radiation emitted from the laser diode is 1.4 μm to 1.8 μm, and the light of this wavelength is sequentially irradiated onto the blood of the subject through the skin. The blood glucose concentration measuring device that does not harm living organisms according to item 1. 3. The light condensing section is made of an integrating sphere formed into a substantially spherical shape with a diameter of 2.56 mm or less, and the overall dimensions are 150 mm in width, 75 mm in length, and 22 mm in height. A blood glucose concentration measuring device that does not harm living organisms as set forth in claim 1. 4. A main body of this blood glucose concentration measuring device and a measuring section consisting of the optical system, a condensing section, and a detecting section are constructed separately, and the main body and the measuring section are connected by an optical fiber. A blood glucose concentration measuring device that does not harm living organisms as claimed in claim 1. 5. The detection section that detects the photons focused by the light focusing section is composed of a germanium detector using a port diode and equipped with a front-stage amplifier, and the D/A converter and A/D converter include:
It is separated from the microphone computer and mounted on the same board, and the power supply is 4.5V~
2. The blood glucose concentration measuring device that does not harm living organisms as claimed in claim 1, characterized in that it is comprised of a 9V charging battery.
Applications Claiming Priority (4)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| KR1989-15584 | 1989-10-28 | ||
| KR1019890015584A KR930011586B1 (en) | 1989-10-28 | 1989-10-28 | Non-invasive method and apparatus for measuring blood glucose concentration |
| KR1990-11241 | 1990-07-24 | ||
| KR1019900011241A KR920002091A (en) | 1990-07-24 | 1990-07-24 | Egg-Invasive Blood Glucose Measurement Method and Apparatus |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH03146032A JPH03146032A (en) | 1991-06-21 |
| JPH0581253B2 true JPH0581253B2 (en) | 1993-11-12 |
Family
ID=26628109
Family Applications (2)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP2286941A Granted JPH03146032A (en) | 1989-10-28 | 1990-10-24 | Method and device for measuring noninvasive blood sugar concentration |
| JP1997007317U Expired - Lifetime JP2588468Y2 (en) | 1989-10-28 | 1997-08-18 | Blood glucose concentration measurement device that does not damage the living body |
Family Applications After (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP1997007317U Expired - Lifetime JP2588468Y2 (en) | 1989-10-28 | 1997-08-18 | Blood glucose concentration measurement device that does not damage the living body |
Country Status (9)
| Country | Link |
|---|---|
| US (1) | US5267152A (en) |
| EP (1) | EP0426358B1 (en) |
| JP (2) | JPH03146032A (en) |
| CN (1) | CN1025410C (en) |
| AT (1) | ATE179874T1 (en) |
| CA (1) | CA2028261C (en) |
| DE (1) | DE69033104T2 (en) |
| HU (1) | HU213438B (en) |
| RU (1) | RU2122208C1 (en) |
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Also Published As
| Publication number | Publication date |
|---|---|
| JP2588468Y2 (en) | 1999-01-13 |
| DE69033104T2 (en) | 1999-10-28 |
| EP0426358A1 (en) | 1991-05-08 |
| HUT58145A (en) | 1992-01-28 |
| CA2028261A1 (en) | 1991-04-29 |
| US5267152A (en) | 1993-11-30 |
| DE69033104D1 (en) | 1999-06-17 |
| HU906914D0 (en) | 1991-05-28 |
| ATE179874T1 (en) | 1999-05-15 |
| RU2122208C1 (en) | 1998-11-20 |
| CA2028261C (en) | 1995-01-17 |
| JPH10181U (en) | 1998-08-25 |
| JPH03146032A (en) | 1991-06-21 |
| CN1051297A (en) | 1991-05-15 |
| HU213438B (en) | 1997-06-30 |
| CN1025410C (en) | 1994-07-13 |
| EP0426358B1 (en) | 1999-05-12 |
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